Medical devices and delivery systems for delivering medical devices

ABSTRACT

Medical devices and delivery systems for delivering medical devices to a target location within a subject. In some embodiments the medical devices can be locked in a fully deployed and locked configuration. In some embodiments the delivery systems are configured with a single actuator to control the movement of multiple components of the delivery system. In some embodiments the actuator controls the independent and dependent movement of multiple components of the delivery system.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No. 12/578,447, filed Oct. 13, 2009, which claims priority under 35 U.S.C. sctn. 119 to U.S. Provisional Patent Application Nos. 61/104,509, filed Oct. 10, 2008; and 61/151,814, filed Feb. 11, 2009; which applications are incorporated by reference in their entirety.

This application is related to the following patent applications, all of which are incorporated by reference herein: U.S. patent application Ser. No. 10/746,240, filed Dec. 23, 2003 (U.S. Patent Publication No. 2005/1237687); U.S. patent application Ser. No. 10/972,287, filed Oct. 21, 2004 (U.S. Patent Publication No. 2005/0137698); U.S. patent application Ser. No. 10/982,692, filed Nov. 5, 2004 (U.S. Patent Publication No. 2005/0137699); U.S. patent application Ser. No. 11/706,549, filed Feb. 14, 2007 (U.S. Patent Publication No. 2007/0203503); U.S. Provisional Patent Application No. 61/104,509, filed Nov. 10, 2008; U.S. patent application Ser. No. 11/274,889, filed Nov. 14, 2005 (U.S. Patent Publication No. 2007/0112355); U.S. patent application Ser. No. 10/870,340, filed Jun. 16, 2004 (U.S. Patent Publication No. 2005/0283231); and U.S. patent application Ser. No. 11/314,969, filed Dec. 20, 2005 (U.S. Patent Publication No. 2007/0118214).

BACKGROUND OF THE INVENTION

Implantable medical devices can be delivered to a target location within a patient and implanted therein. For example, endoluminal delivery techniques are well known. The delivery system typically includes a sheath and/or a catheter through which the implant is delivered to the target location. The implant is generally deployed from the sheath or catheter at the target location. Some implantable devices are completely self-expanding; they self-expand when released from the sheath or catheter and do not require any further expansion after the self-expanding step. The self-expansion can occur by proximally retracting the sheath or catheter, by pushing the implantable device from the sheath or catheter, or a combination thereof. Some implantable devices, however, are configured and adapted to be actuated during or after the self-expansion step. Exemplary replacement heart valves which can be actuated after a self-expansion step can be found described in co-pending application Ser. No. 10/982,388, filed Nov. 5, 2004, and application Ser. No. 10/746,120, filed Dec. 23, 2003, the disclosures of which are hereby incorporated by reference herein. It may be advantageous to lock an expandable medical device in a fully deployed and locked configuration to secure the device in the deployed.

During the delivery process the medical device can be actuated by the delivery system using one or more actuators. For example, an actuator (e.g., in the form of a knob on a handle of the delivery system) may be actuated (e.g., turned) to cause a component of the delivery system to move relative to another component in the delivery system or relative to the implantable device, or both. It is generally desirable to make the delivery process as easy as possible for the physician, reduce the time needed to complete the procedure, and reduce the mechanical complexity of the delivery system. In some delivery procedures, multiple components of the delivery system need to be actuated to deploy the implant. It may also be necessary to ensure that multiple steps are carried out in a certain order. What are needed are delivery systems which can simplify the deployment procedure of the medical device and/or ensure that multiple steps are performed in a certain order.

SUMMARY OF THE INVENTION

One aspect of the disclosure describes a medical device system, including a delivery system comprising a housing disposed external to a subject, wherein the housing comprises an actuator, wherein the delivery system is configured and arranged such that the actuator is adapted to move a first delivery system component independently of a second delivery system component, and wherein the delivery system is further configured and arranged such that actuator is also adapted to move the second delivery system component independently of the first delivery system component.

In some embodiments the delivery system is further configured and arranged such that the actuator is further adapted to actuate the first delivery system component and the second delivery system component simultaneously, and is some instances at different rates when actuating them simultaneously.

In some embodiments the delivery system is configured such that actuation of the actuator moves the first and second delivery system components in the same direction. In some embodiments the delivery system is configured such that actuation of the actuator actuates the first and second delivery system components in a specific sequence.

In some embodiments the actuator is a single actuator element, and wherein the actuator is configured such that actuation of the actuator in a single type of motion causes both the actuation of the first delivery system component independent of the second delivery system component and the actuation of the second delivery system component independent of the first delivery system component.

In some embodiments the first delivery system component is a delivery sheath, and wherein the medical device system comprises a medical device adapted to be percutaneously delivered to a target location in a patient through the delivery sheath, and wherein the actuator is adapted to move the delivery sheath independently of and prior to the independent movement of the second delivery system component. The second delivery system component can be reversibly coupled to a portion of the medical device. The actuator can be adapted to independently move both the sheath and the second delivery component proximally when actuated. Actuation of the actuator can be configured to proximally retract the sheath to allow the medical device to expand, and wherein further actuation of the actuator retracts the second delivery system component proximally.

In some embodiments the delivery system and actuator are configured such that movement of the actuator in a singular type of motion, such as rotation in a single direction, moves the first delivery system component independently of a second delivery system component and moves the second delivery system component independently of the first delivery system component. The singular type of motion can move the first delivery system component independently of a second delivery system component and moves the second delivery system component independently of the first delivery system component without any intervening actuation steps being performed between the independent movement of the first delivery system component and the independent movement of the second delivery system component.

One aspect of the disclosure is a method of using a delivery system to deploy a medical device in a patient. The method includes providing a delivery system comprising a housing disposed external to the patient, wherein the housing comprises an actuator, actuating the actuator to move a first delivery system component independently of a second delivery system component, and actuating the actuator to move the second delivery system component independently of the first delivery system component.

In some embodiments the further comprises actuating the actuator to move the first and second delivery system components simultaneously. In some embodiments actuating the actuator comprises actuating the actuator in a singular type of motion to move the first and second delivery system components independently of one another, as well as to move the first and second delivery system components simultaneously. Actuating the actuator can move the first and second delivery system components at different rates at least during a portion of the time they are being moved simultaneously.

In some embodiments actuating the actuator moves the first and second delivery system components in the same direction. In some embodiments actuating the actuator moves the first and second delivery system components in a specific sequence.

In some embodiments actuating the actuator comprises actuating the actuator in a singular type of motion, such as rotation in a single direction, to move both the first and second delivery system components independently of one another.

In some embodiments the first delivery system component is a delivery sheath, and wherein actuating the actuator comprises moving the delivery sheath in a proximal direction independently of and prior to the independent movement of the second delivery system component. The second delivery system component can be reversibly coupled to a medical implant, and wherein actuation of the second delivery system component independently moves the second delivery system component in a proximal direction independently of and subsequent to the proximal movement of the delivery sheath.

In some embodiments moving the first and second delivery system components comprises moving the first and second delivery system components proximally.

In some embodiments actuating the actuator to move the first delivery system component comprises moving a delivery sheath proximally to allow the medical device to expand.

One aspect of the disclosure is a delivery system for deploying a medical device in a patient. The system includes a delivery sheath, a delivery catheter adapted to be disposed within the sheath and movable relative to the sheath, a coupling member adapted to be reversibly coupled to a portion of a medical device, wherein the medical device is adapted to be percutaneously delivered to a target location in a patient through the delivery sheath, wherein the delivery sheath is adapted to be moved relative to the medical device to release the medical device from the sheath, and a sheathing assist element, at least a portion of which is disposed between a distal end of the sheath and a proximal portion of the medical device when the delivery sheath is sheathing at least the proximal portion of the medical device.

In some embodiments a proximal portion of the sheathing assist element is attached to a distal region of the delivery catheter. In some embodiments a proximal end of the coupling member is attached to the distal region of the delivery catheter.

In some embodiments a proximal end of the sheathing assist element is attached to a distal region of the delivery catheter, and wherein a proximal end of the coupling member is attached to the distal region of the delivery catheter, and wherein the sheathing assist element is radially outward relative to the coupling member.

In some embodiments the sheathing assist element comprises a plurality of looped elements, wherein a first one of the looped elements has a length that is different than the length of a second one of the looped elements.

In some embodiments the medical device comprises a braided element, and wherein the sheathing assist element comprises a plurality of sheathing assist elements, wherein a first of the plurality of sheathing assist elements is disposed radially outward of a proximal end of the braided element when the sheath is sheathing the braided element, and wherein a second of the plurality of sheathing assist elements extends through the braided element.

One aspect of the disclosure is a method of sheathing a medical device within a delivery sheath. The method includes positioning a sheathing assist element between a portion of an expandable medical device and a delivery sheath, and moving the delivery sheath distally relative to the sheathing assist element and the medical device to assist in the collapse of at least a portion of the expandable medical device within the delivery sheath.

In some embodiments the positioning step comprises positioning the sheathing assist element between at least a proximal end of the expandable medical device and the distal end of the delivery sheath to reduce the likelihood that the distal end of the sheath will get caught on the proximal end of the medical device as the delivery sheath is moved distally relative to the sheathing assist element.

In some embodiment the delivery system further comprises a coupling member, the method further comprising maintaining a reversible coupling between the coupling member and the medical device, wherein positioning the sheathing assist element comprises positioning the sheathing assist element radially outward relative to the coupling member.

In some embodiments moving the delivery sheath distally relative to the sheathing assist element causes a radially inward force to be applied from the sheathing assist element to the portion of the expandable medical device.

INCORPORATION BY REFERENCE

All publications and patent applications mentioned in this specification are hereby incorporated by reference herein to the same extent as if each individual publication or patent application was specifically and individually indicated to be incorporated by reference.

BRIEF DESCRIPTION OF THE DRAWINGS

The novel features of the invention are set forth with particularity in the appended claims. A better understanding of the features and advantages of the present invention will be obtained by reference to the following detailed description that sets forth illustrative embodiments, in which the principles of the invention are utilized, and the accompanying drawings of which:

FIG. 1A shows an exemplary replacement heart valve in a deployed and locked configuration.

FIG. 1B shows an exemplary replacement heart valve in a collapsed and delivery.

FIG. 2A illustrates an exemplary medical device delivery system reversibly coupled to a medical device, wherein the medical device is in a collapsed configuration.

FIG. 2B shows an exemplary medical device delivery system reversibly coupled to a medical device, wherein the medical device is in a deployed and locked configuration.

FIGS. 3A-3G illustrate an exemplary medical device deployment and locking procedure.

FIG. 4 shows an exemplary replacement heart valve reversibly coupled to a portion of a delivery system.

FIGS. 5A-5E show an exemplary lock and release mechanism for a medical device.

FIGS. 6A and 6B show an exemplary reversible coupling mechanism between a delivery system and a medical device.

FIGS. 7A-7D shows an exemplary lock and release mechanism of a medical device.

FIGS. 8A-8G shows an exemplary lock and release mechanism of a medical device.

FIG. 9 shows an exemplary reversible coupling mechanism between a delivery system and a medical device.

FIG. 10 shows an exemplary reversible coupling mechanism between a delivery system and a medical device.

FIGS. 11A-11D show an exemplary lock and release mechanism of a medical device.

FIGS. 12A-12C show an exemplary lock and release mechanism of a medical device.

FIGS. 13-14E show an exemplary lock and release mechanism of a medical device.

FIGS. 15A-16B show an exemplary lock and release mechanism of a medical device.

FIGS. 17A-17D illustrate a portion of an exemplary delivery system in which a single handle actuation element can move two different delivery system components independently of one another.

FIG. 18A-18D illustrate an varying pitch design to vary the rate of travel of an actuation element.

FIG. 19 illustrates an exemplary barrel-cam design to control the rate of movement of delivery system components.

FIGS. 20A-20C illustrate a portion of an exemplary delivery system in which a single handle actuation element can move two different delivery system components independently of one another.

FIGS. 21-22 illustrate exemplary designs for decoupling the motion of the rods and outer sheath.

FIGS. 23A-23C illustrate actuating a second actuator to control movement of different portions of the medical device delivery process.

FIGS. 24-41 illustrate a variety of medical device sheathing assist elements.

DESCRIPTION OF THE INVENTION

The present disclosure describes medical devices and delivery systems for delivering medical devices to a target location in a subject. The medical devices can be implantable or they can be adapted to be temporarily positioned within the subject. The delivery systems can be adapted to deliver a wide variety of suitable medical devices to a target location in a subject, but in some embodiments are configured for minimally invasive delivery procedures, such as endovascular procedures. In some embodiments the medical device is a replacement heart valve (e.g., a replacement aortic heart valve), and the delivery system is configured to deliver the replacement heart valve endovascularly to replace the functionality of the subject's native heart valve.

FIGS. 1A and 1B show replacement heart valve 10 including anchoring element 12, shown comprising a braided material, and replacement valve leaflets 14 (not shown in FIG. 1B for clarity). Replacement heart valve 10 also includes three first locking members 16, also referred to herein as posts, and three second locking members 18, also referred to herein as buckles. Three posts and three buckles are shown, each post being associated with one of the buckles. FIG. 1A shows anchoring element 12, also referred to herein an anchor, in a fully deployed configuration in which anchoring element 12 is locked and maintained in the deployed configuration by the locking interaction between first locking members 16 and second locking members 18. FIG. 1B shows replacement heart valve 10 in a collapsed delivery configuration in which the replacement heart valve is delivered within a delivery system to a target location within the subject (delivery system not shown).

In this embodiment valve leaflets 14 are attached to posts 16 at the valve's three commissures. Posts 16 therefore support the valve within the anchoring element. The posts and buckles (or other suitable first and second locking members) are both coupled to the anchor. When the anchoring element 12 is in the collapsed configuration as shown in FIG. 1B, each locking element of posts 16 which is configured to lock with a corresponding locking element of buckles 28 is located distally relative to the locking element of the buckle to which is it to adapted to be locked. Stated alternatively, the locking elements of the buckles which are configured to lock to the locking elements of the posts are located proximally to the locking elements of the posts in the delivery configuration.

FIGS. 2A and 2B illustrate an exemplary embodiment of a delivery system 100 and components thereof which can be used to deliver and deploy a medical device at a target location in a subject. Delivery system 100 includes handle 120, sheath 110, catheter 108 disposed with sheath 110, and actuation elements 106A and 106B which are reversibly coupled to replacement heart valve 10. In FIG. 2A, heart valve 10 is in a collapsed delivery configuration (also shown in FIG. 1B) within sheath 110. Delivery system 100 also includes guidewire G and nosecone 102. In some embodiments catheter 108 has central lumen 109 and a plurality of circumferentially disposed lumens Lu.

In FIGS. 2A and 2B, the plurality of actuation elements 106A are shown reversibly coupled to a proximal region of anchoring element 12. Specifically, actuation elements 106A are reversibly coupled to the proximal end of the anchoring element 12 via a reversible coupling mechanism. Actuation elements 106B are reversibly coupled to a region of the replacement heart valve distal to the proximal end of the anchoring element. Specifically, actuation elements 106B are shown reversibly coupled to posts 16 via a reversible coupling mechanism. Details of this and similar embodiments can be found in U.S. Patent Publication Nos. 2005/0137686 and 2005/0143809, the disclosures of which are incorporated by reference herein.

In the embodiments shown in FIG. 1A-2B, the anchoring element comprises a braided material, such as nitinol, and is formed of one or more strands of material. In one embodiment the anchoring element 12 is formed of a shape memory material and is heat set in a self-expanded configuration, such that when the anchoring element is deployed from the sheath of the delivery system, the braid will begin to naturally begin to shorten and expand from the collapsed delivery configuration to the memory self-expanded configuration. The self-expanded configuration can be thought of as an at-rest or partially deployed configuration, and is described in more detail in U.S. Patent Publication Nos. 2005/0137686 and 2005/0143809. Once the anchoring element has expanded to the partially deployed configuration, at least one of the actuators 106A and 106B is actuated via an actuator on a handle disposed external to the patient. As is described in more detail in U.S. Patent Publication Nos. 2005/0137686 and 2005/0143809, actuators 106B can be actuated in the proximal direction relative to the actuation elements 106A, which applies a proximally directed force to the posts, which applies a proximally directed force to a distal region of the anchoring element. Actuators 106A can, alternatively or in addition to the proximally directed force, be actuated in a distal direction to apply a distally directed force on a proximal region of the anchoring element. The axially directed forces actively foreshorten the anchoring element, moving the posts closer to the buckles until the posts and buckles lock together to lock the anchoring element in a fully deployed and locked configuration. The locked configuration is therefore shorter than the partially-deployed configuration.

FIGS. 3A-3G illustrate an exemplary method of delivering a replacement aortic heart valve in a delivery configuration and deploying it from a delivery sheath to a fully deployed and locked configuration. In this embodiment actuation elements 106B are reversibly coupled to the posts of the replacement valve, but actuation elements 106A, which may also be referred to herein as “fingers,” are reversibly coupled to the buckles. There are three actuation elements 106A reversibly coupled to the three buckles, and there are three actuation elements 106B reversibly coupled to the three posts. As seen in FIG. 3A, replacement valve 10 is delivered in a collapsed delivery configuration within sheath 110 in a retrograde fashion through aorta A over guidewire G and placed across a patient's aortic valve using known percutaneous techniques.

Once sheath 110 is positioned across the native valve as shown in FIG. 3A, sheath 110 is retracted proximally relative to the replacement valve using an actuator on the delivery system handle which is disposed external to the patient (examples of which are described in detail below). As the sheath is withdrawn, as seen in FIG. 3B, the distal portion of anchoring element 12 begins to self-expand due to the material properties of the anchoring element. The anchoring element can have a memory self-expanded configuration such that as the sheath is withdrawn the anchor begins to self-expand, or return to its memory configuration. As the sheath continues to be retracted proximally, the anchoring element continues to self-expand, as shown in FIGS. 3C and 3D. In FIG. 3E the sheath has been retracted proximally such that the distal end of the sheath is disposed proximal to the distal end of fingers 106A. In FIG. 3E the sheath is not retracted far enough proximally to allow the fingers to self-expand. As such, although the anchoring element is completely out of the sheath, the proximal end of the anchor does not expand towards its memory configuration. Only after the sheath has been retracted past the distal end of catheter 108 can the fingers fully self-expand, as is shown in FIG. 3F. This allows the proximal end of the anchoring element to expand. 100601 The anchoring element is then actively foreshortened (and potentially further expanded) to the fully deployed and locked configuration shown in FIG. 3G by the application of axially directed forces (proximally and distally directed). To actively foreshorten the anchoring element, a proximally directed force is applied to posts via actuation elements 106B (not shown in FIGS. 3A-3G but which are coupled to the posts), and/or a distally directed force is applied to buckles via actuation elements 106A. In one embodiment a proximally directed force is applied to posts through actuation elements 106B, and fingers 106A are held in position to apply a distally directed force to the buckles. This active foreshortening causes the posts and buckles to move axially closer to one another until they lock together, which maintains the anchoring element in a fully deployed and locked configuration in FIG. 3G. The actuation elements 106A and 106B are then uncoupled released from the buckles and posts, respectively, and the delivery system is then removed from the subject. The details of exemplary locking processes and release processes are described in detail below. Additional details of delivery, deployment, locking, and release processes that may be incorporated into this and other embodiments can be found in U.S. Patent Publication No. 2005/0137699, filed Nov. 5, 2004, U.S. Patent Publication No. 2007/0203503, filed Feb. 14, 2007, and U.S. Patent Publication No. 2005/0137697, filed Nov. 21, 2004, each of which is incorporated by reference herein.

FIG. 4 shows replacement heart valve 10 and a distal portion of the delivery system, including catheter 208, which were described in reference to FIGS. 3A-3G. Heart valve 10 is in a fully deployed and locked configuration, with actuation elements 206A (“fingers”) and 206B still reversibly coupled to buckles 18 and posts 16, respectively. The configuration and arrangement in FIG. 4 is therefore similar to that shown in FIG. 3G. The commissure portions of leaflets 14 are affixed to the three posts 16, while posts 16 are moveably coupled to anchoring element 12 (e.g., via sutures or wires) at a location distal to the proximal end of anchoring element 12. Replacement heart valve 10 also includes buckles 18 (three are shown) which are affixed (but may be moveably coupled to the anchor similar to the posts) to anchor 12 (e.g., via wires or sutures) at a proximal region of anchor 12. In FIG. 4, the actuation elements 206B are reversibly coupled to posts 16, while actuation elements 206A are reversibly coupled to buckles 18. The delivery system also includes three actuator retaining elements 210, each of which are adapted to receive therein an actuation element 206B and an actuation element 206A. Actuation elements 206A are shown attached at their proximal end to the distal end of catheter 208, while actuation elements 206B are configured and arranged to move axially within catheter 208. Actuation elements 206B therefore are configured and arranged to move axially with respect to actuation elements 206A as well. Fingers 206A and actuation elements 206B are maintained closely spaced to one another (at least while the delivery system is coupled to the replacement valve) with actuator retaining elements 210. Retaining elements 210 have a lumen therein in which fingers 206A are disposed and through which the actuation elements 206B can be actuated axially. Fingers 206A are shown disposed radially outward relative to the actuation elements 206B, which are shown as generally cylindrical rods. The replacement heart valve in FIG. 4 has not been released from the delivery system.

FIGS. 5A-5E illustrate the process of uncoupling the delivery system from the heart valve shown in FIG. 4 (anchoring element is not shown). In FIG. 5A post 16 has an elongated locking portion 17 which is adapted to be pulled into an internal channel within buckle 18. Locking portion 17 of post 16 has a locking element in the shape of a groove which is adapted to receive a tooth on the buckle 18. As the post is pulled into the buckle, the tooth on the buckle will engage the groove on the post and lock the post and buckle together, maintaining the anchoring element in a locked configuration. This configuration is shown in FIG. 5A. In this configuration, actuation element 206B (or “rod”) is reversibly coupled to post 16. Rod 206B includes a portion that is disposed within a channel in post 16 such that bore 230 (see FIG. 5E) in the distal portion of rod 206B is aligned with bore 232 in post 16. Pin 234, which is part of pin assembly 236 as can be seen in FIG. 4, extends through both rod bore 230 and post bore 232 to couple the rod to the post. The distal portion of pin assumes a curled or looped configuration, which prevents rod 206B from disengaging from post 16. In FIG. 5A finger 206A is reversibly coupled to buckle 18 via the interaction between tooth 239 on buckle 18 and groove 238 on finger 206A (see FIG. 5E). In FIG. 5A, collar 22 is positioned over the engagement between tooth 239 and groove 238 to retain the 206A and buckle 18 in a reversibly coupled configuration.

Once it has been determined to release the heart valve in place within the subject, pin 234 is first removed by retraction of pin assembly 236 (see FIG. 4) in the proximal direction, which pulls the pin through bores 230 and 232 and uncouples rod 206B from post 16, which is shown in FIG. 5B. Next, rod 206B is pulled back in the proximal direction via actuation of an actuator on the delivery system handle. Once rod 206B has been pulled to the position in FIG. 5C, collar engagement 23 engages collar 22 and pulls it in the proximal direction along with rod 206B. This causes the collar to be pulled proximally from the position in FIG. 5C to the position in FIG. 5D. Retracting the collar to the position in FIG. 5D allows tooth 239 of the buckle to disengage groove 238 with continued retraction of rod 206B, which is shown in FIG. 5E. Both rod 206B and finger 206A are uncoupled from the heart valve, and the delivery system is now retracted from the patient with the medical device implanted in place.

In some embodiments the axially directed force vectors applied by the fingers 206A to the buckles and the rods 206B to the posts can be in substantially opposite directions to enhance the efficiency of the foreshortening and locking process. An advantage of coupling the fingers directly to the buckles is that the buckles are better aligned with the posts during the foreshortening and locking process. This can help ensure that the post, when pulled proximally, will better align with the buckle such that the post can be efficiently locked with the buckle. When using an anchor that may become twisted or distorted under high foreshortening and locking forces (such as an anchor comprising a braided material), it can be beneficial to ensure that a buckle which is coupled to the anchor (and thus may fall out of alignment with the post) remains properly aligned with the post. Directly coupling the fingers to the buckle can provide these benefits. This can also increase the general efficiency of proximally directed pulling forces because less force may be required to pull and lock the posts with the buckles. When incorporating actuators on a handle to control delivery and deployment of a medical device, reducing the amount of force that is needed to be applied to the handle actuator can simplify the delivery system design.

FIGS. 6A and 6B illustrate an alternative embodiment of post 250 which is reversible coupled to actuation element 252. FIG. 6B is a partially exploded view identifying the components shown in FIG. 6A. Actuation element 252 includes rod 254, tab deflector 256, and retaining clip 258. Rod 254 can be actuated in a proximal direction P by actuating an actuator on a handle disposed external to the patient as described herein.

Rod 254 is attached to tab deflector 256 and to retaining clip 258. Rod 254 includes, at its distal end, catch 260, which engages with clip element 262 of retaining clip 258. Post 250 has an internal channel therein adapted to slidingly receive retaining clip 258 and tab deflector 256, each of which are adapted to receive rod 254 therein. Tab deflector 256 includes rib element 264. Retaining clip 258 includes clip feet 266. To lock the anchoring element (not shown), rod 254 is pulled in the proximal direction and clip feet 266 engage the distal end of post 250 and pull it in the proximal direction towards the buckle (not shown).

FIGS. 7A-7D show side-views of an exemplary locking sequence of post 250 shown in FIGS. 6A and 6B to buckle 268 (anchor not shown). FIG. 7A shows rod 254 being actuated in the proximal directed by an actuation force generated from an actuator on the handle of the delivery system external to the patient. In FIG. 7A, post 250 is still distal to buckle 268. As rod 254 continues to be pulled in the proximal direction, catch 260 (shown in FIG. 6B) applies a proximally directed force to clip element 262 (shown in FIG. 6B). This causes clip feet 266 to apply a proximally directed force to the distal end of post 250. This causes the post to move in the proximal direction. Post 250, tab deflector 256, and retaining clip 258 thus move towards buckle 268, as is shown in FIG. 7A.

Continued actuation of the actuator external to the patient causes the post, the deflector, and the clip to be pulled further in the proximal direction into a position within a channel within buckle 268, as is shown in FIG. 7B. Because rib element 264 of tab deflector 256 is disposed adjacent groove 272 of post 250, rib element 264 prevents buckle tooth 270 from engaging groove 272 of post 250 (shown in FIG. 7B). This prevents the post from locking with the buckle until the physician determines that it is appropriate to do so. Rib element 264 thereby acts as a lock prevention mechanism. The post (and thus the anchor) can be moved distally to lengthen the anchoring element at this point by applying a distally directed force on post 250 using the actuator on the handle.

Once the desired position of the anchor has been obtained, rod 254 continues to be actuated in the proximal direction. This can be done using the same actuator on the handle or a different actuator as described in more detail below. The continued proximal force to rod 254 causes feet 266 to be pinched inwards towards one another to thereby disengage and uncoupled them from the distal end of post 250. This pulls feet 266 within the distal opening of post 250. This releases clip 258 from post 250 and uncouples the rod, deflector, and clip from the post. Continued actuation of the actuator will move the cable, deflector and clip in the proximal direction to the position shown in FIG. 7C. Rib element 264 is disposed proximal to tooth 270 and groove 272 and thus no longer prevents them from locking together. The tooth therefore engages the groove, locking the post to the buckle (shown in FIG. 7C). The anchor (not shown) is now locked in the fully deployed and locked configuration. Continued actuation of rod 254 pulls the rod, clip, and deflector from the patient, as is shown in FIG. 7D.

FIGS. 8A-8G illustrate a side view of a locking and release sequence of an alternative embodiment of a post, buckle, and actuation elements. The system includes actuation element 280 in the form of a rod, buckle 282, post 286, and clip 290. The clip 290 includes feet 294 and rib element 292. Actuation of an actuator on the handle causes rod 280 to be pulled in the proximal “P” direction, as shown in FIG. 8A. Continued actuation pulls rod 280, post 286, and clip 290 through a channel within buckle 282, as shown in FIG. 8B. As rod 280 continues to be pulled, a surface of buckle tooth 284 slides over surface 295 of clip 290, as shown in FIG. 8B. Feet 294 engage the distal end of buckle 282, as shown in FIG. 8C. The top view of this position is shown in FIG. 8G. Between the positions shown in FIGS. 8B and 8C, rib element 292 has prevented the post from locking with the buckle. In the position shown in FIG. 8C, tooth 284 is engaging surface 287 of post 286. The location of feet 294 ensures post groove 288 has been pulled far enough proximally before the clip 290 is removed from the post. From the position shown in FIG. 8C, continued proximal movement of rod 280 will cause feet 294 to pinch together and retract into the channel in buckle 282. This releases clip 290 from post 286 and pulls the rod and clip in the proximal direction. Once the clip is released from the post, the post will begin to naturally move in the distal direction because the anchoring element (not shown, but in this embodiment comprises a braided material) begins to revert naturally to a self-expanded, partially deployed memory configuration (which is more fully described in the applications incorporated by reference herein). As the post begins to move distally, tooth 284 engages post groove 288 as is shown in FIG. 8E. This locks the post and buckle and locks the anchoring element in a fully deployed and locked configuration. The rod and clip can now be removed from the patient, as is shown in FIG. 6F.

FIGS. 9 and 10 show two alternative embodiments incorporating features of the lock and release embodiments above. The embodiment in FIG. 9 is similar to that shown in FIGS. 5A-5E, although rod 304 includes feet 306 which are similar to the feet shown in the embodiments in FIGS. 6A-8G. In this embodiment pin 234 from FIGS. 5A-5E is not needed, as the release of rod 304 from post 300 occurs when rod 304 is pulled proximally, causing feet 306 to pinch inwards and disengage from the post.

FIG. 10 shows an alternative embodiment which incorporates compressible feet 316 at the distal end of rod 314 and release pin 318 (actuated in the same way as shown in the embodiment in FIGS. 5A-5E). The embodiment in FIG. 10 can be thought of as a hybrid design between that shown in FIGS. 5A-5E and 9. One difference between the embodiment in FIGS. 5A-5E and 10 is that in FIGS. 5A-5E there is a slot 230 in the rod that pins the rod to the post. When pin 234 is under tension in FIGS. 5A-5E, the pin is in shear, which increases the likelihood of damaging the pin. In the design in FIG. 10, the slot 230 is not present, but rather the two feet 306 simply extend distally from a distal portion of the rod. Pin 318 maintains feet 316 in the spread-apart position shown in FIG. 10, essentially holding them open and maintaining the coupling between the feet and the post. In this design, the pin is in compression between the feet, rather than being in shear. Once the pin removed, a lower release force can then be applied to the rod to cause the feet to uncouple from the post. Having the pin in compression rather than shear is less likely to cause damage to the pin.

Each of FIGS. 11A-11D shows a side view and perspective view, respectively, of an alternative embodiment including post 320 and actuation element 322 in a sequence wherein post 320 changes configuration from a position in which it is not locked to a corresponding buckle 321 to a locked position, and in which the actuation element 322 is released from the post. Buckle 321 is not shown in the sequence for clarity, although buckle 321 is shown in FIG. 11A to display the relative positions of the post, actuation element, and buckle. FIGS. 12A-12C show the locking and release sequence including buckle 321.

In FIG. 11A actuation element 322 is reversibly coupled to post 320. Actuation element 322 includes rod 324, post lock prevention element 326, and post lock actuator 328. Post 320 includes post lock element 330. FIG. 11A illustrates an initial configuration of the respective components before the post is pulled towards the buckle. To actively foreshorten the anchoring element (not shown), the rod 324 is retracted in the proximal direction. Post lock prevention element 326 is initially engaged with post lock element 330, and thus proximal retraction of rod 324 causes proximal movement of post 320. Rod 324 continues to be pulled proximally until post 320 is pulled within buckle, as can be seen in FIG. 12A. In FIG. 12A the post is not yet locked to the buckle, and post lock element 330 is proximal to buckle lock element 332. To lock post 320 to buckle 321, a separate actuator (not shown) is actuated to retract the post lock prevention element 326 in the proximal direction to disengage post-lock prevention element 326 from post lock element 330, as shown in FIGS. 11B and 12B. Alternatively, rod 324 and post lock prevention element 326 may be engaged in a manner such that a continued proximal force applied to rod 324 will disengage post lock prevention element 326 from post lock element 330. Because the anchoring element has a memory configuration that is longer than the fully expanded and deployed configuration, once post-lock prevention element 326 is disengaged from post lock element 330, the anchor will attempt to return to its elongated memory configuration. Thus, post 320 begins to move in the distal direction. Distal movement of post 320 causes post-lock actuator 328 to apply a radially outward force to post lock element 330, moving it to a locked configuration shown in FIGS. 11C and 12C. Alternatively, or in addition to, once lock prevention element 326 is disengaged from post lock element 330, continued proximal retraction of rod 324 causes post-lock actuator 328 to apply a radially outward force on post lock element 330. Continued distal movement of post 320 causes post lock element 330 to engage with buckle lock element 332, locking post 320 to buckle 321. The lock prevents further distal movement of the post relative to the buckle, locking the anchor in an axially compressed and fully deployed configuration. Actuation element 322 can now be withdrawn proximally and removed from the patient.

FIG. 13 shows an alternative embodiment of post 340 and clip 342, which includes deformable element 344. FIGS. 14A-14E show a sequence of locking post 340 to buckle 348 and releasing clip 342 from post 340. A rod (not shown) is attached to clip 342, similar to the embodiments described above. In the position shown in FIG. 14A, the proximal end of deformable element 344 engages surface element 346 of post 340. This engagement maintains the clip within the post as the clip is pulled proximally. This engagement also pulls the post proximally as the clip is pulled proximally. As the actuator is actuated the cable pulls the post and clip within the buckle 348 as shown in FIG. 14B. Continued actuation from the position shown in FIG. 14C causes tooth 350 of buckle 348 to engage and deform deformable element 344. Deforming element 344 allows tooth 350 to engage groove 352 to lock the buckle and post. This step also releases deformable element 344 from engagement with surface 346, thus releasing the clip from the post, as is shown in FIG. 14D. This step therefore also releases the rod and clip from the post. FIG. 14E shows the clip completely withdrawn proximally from the post.

FIGS. 15A, 15B, 16A, and 16B illustrate an alternative embodiment of the post lock and release mechanism. The embodiment in FIGS. 15A-16B works similarly to those described above in that an actuator is actuated to pull the actuation element, or rod, which pulls the post towards the buckle to lock the anchoring elements. Rod 354 includes a clip similar to the clip in the embodiment in FIGS. 6A and 6B. FIG. 15A is a perspective view and FIG. 15B is a side view after rod 354 has been actuated and pulled proximally such that tooth 358 of buckle 352 is locked with groove 362 of post 360. Prior to the position shown in FIGS. 15A and 15B, surface 356 of rod 354 prevented tooth 358 from locking with the groove in the post. The clip at the distal end of the rod is engaged with a deformable element of the post such that continued actuation of the rod causes the deformable element to deform and release the post from the rod. This rod can then be removed from the patient by continued actuation of the actuator. Alternatively, a pin similar to pin 234 in FIGS. 5A-5E can be incorporated into the embodiment, such that the pin is removed when it is desirable to release the rod from the post, as is described above.

FIGS. 16A and 16B illustrate an unlocking of the post and buckle which are locked in FIGS. 15A and 15B. This unlocking step must be performed before the heart valve is released from the delivery system. Rod 354 is pushed distally, causing surface 364 (unlocking element) of the rod to engage and disengage tooth 358 from the groove in the post. Continued distal movement of the rod pushes the post in a distal direction, which lengthens the anchoring element.

In some embodiments, the fingers can be made of an alloy that is heat set to a memory expanded configuration. The rods can comprise, for example, stainless steel. The outer tube can be made of, for example, a heat-shrink polymer, but can be any suitable material. The outer tube provides enhanced column strength to the fingers, which can be advantageous when under the forces applied during the active foreshortening of the anchoring element.

In the embodiments above reference was made to a delivery system handle disposed external to the subject, which is used to control the actuation of the actuation elements and the sheath. The deployment of the medical implant as described herein can be controlled by actuators (e.g., knobs, levers, etc) on the handle, which are actuated by the physician to control the deployment of the device. It may be desirable to be able to perform multiple deployment steps with as few actuators as possible to simplify the delivery and expansion process. It may further be desirable to perform certain deployment steps with a single actuator, perhaps even actuating a single actuator with a singular type of movement (e.g., rotating a knob in a single direction) to perform multiple parts of the deployment process. This can make the procedure easier for the physician because a hand used to actuate the handle actuator does not need to be removed from the actuator to perform multiple steps. In some embodiments of the delivery system described below, the actuation steps of unsheathing the anchoring element and locking the posts with buckles are performed with a single actuator on a handle of the delivery system. Having a single actuator on the handle which can perform multiple deployment steps can simply the overall procedure. Using a single actuator to control multiple deployment steps can also insure that the steps are performed in a specified sequence, and making sure that a second step does not occur before the occurrence of a first step.

In embodiments described herein in which actuation of a single actuator in a singular type of motion moves a plurality of delivery system components, the singular type of motion can be performed to move more than one delivery system component without any other intervening actuation step being performed. In some embodiments, the user can stop the actuation of the actuator in the singular type of motion, and then continued the actuation. A singular type of motion includes embodiments in which a period of time passes without any actuation. That is, the user may start to actuate the actuator, wait a period of time (for example, to determine if the position of the medical device is sufficient based on an imaging technique), then continue to actuate the actuator. This falls under the “singular” type of motion as described here.

A potential challenge in using a single actuator to actuate multiple components of a delivery system arises when the actuatable components are to be actuated independently of one another, or when they are to be actuated independently of one another during portions of the procedure but actuated at the same time during other portions of the procedure, or when they must be actuated at the same time but at different rates of movement. Provided below are delivery systems in which actuation of a single actuator actuates a plurality of delivery system components wherein a first of the plurality of components and a second of the plurality of components are each actuated independent of the other. In some embodiments the first and second components are also adapted to be actuated at the same time as one another, and in some embodiments at different rates while they are both being actuated.

In some embodiments of the delivery system, a single actuator is used to both proximally retract the sheath during the unsheathing process (for example, as shown in the exemplary method in FIGS. 3B-3F) and to proximally retract the actuation elements which are coupled to the posts. That is, a single actuator is actuated in a single manner to both unsheath the implant as well as to lock the implant in a fully deployed and locked configuration. Incorporating a single actuator into the delivery system which can be actuated in one direction or manner to both deploy the implant from the sheath as well as reconfigure it to its final deployed configuration can greatly simplify the deployment procedure for the physician.

During a first portion of the deployment of the implant only the sheath is pulled in the proximal direction, which unsheathes the implant. During a second portion of the deployment only the posts are pulled proximally, which moves the posts towards the buckles to lock the anchoring element in the locked configuration. During a third portion of the procedure both the sheath and the actuation elements reversibly coupled to posts are pulled in the proximal direction, which may result in variable rates of movement of the sheath and the actuation elements. The single actuator must therefore account for both the dependent and independent motions of a plurality of delivery system components.

FIGS. 17A-17D illustrate an exemplary delivery system in which a single actuator on a handle selectively actuates a plurality of delivery system components. While this delivery system design can be used to selectively actuate a plurality of delivery system components in almost type of medical device delivery system, it will be described in relation to deployment of a replacement heart valve. In addition, while the single actuator can be adapted to actuate different types of components than those which are described herein, it will be described as controlling the movement of a sheath and an actuation element which actuates a portion of a replacement heart valve.

FIGS. 17A-17D show components of delivery system 370 which are housed inside a handle housing (not shown), including outer tube 380, rotary actuator 372 (which is adapted to be actuated by a user), lead screw 374, rod carriage 376, rod carriage screw 378, sheath carriage 384, sheath carriage screw 386. Proximal movement of rod carriage 376 moves the rods in the proximal direction, which causes a proximally directed force to be applied to the posts described herein (and distal movement of post puller carriage 206 causes a distally directed force to be applied to the posts). Proximal movement of sheath carriage 384 causes the sheath to be retracted proximally to unsheathe the implant (and distal movement of sheath carriage 384 causes the sheath to be moved distally to re-sheath the implant). In one embodiment, the sheath has an adapter bonded to its proximal end which is screwed to the sheath carriage. Movement of the sheath carriage, through rotation of the lead screw, therefore directly moves the sheath. In one embodiment the rods are bonded inside a hypotube and the hypotube is pinned to a force limiting member, which is directly attached to the rod carriage. Movement of the rod carriage therefore moves the rods. Rotation of rotary actuator 372 translates rotational movement into linear movement of rod carriage screw 378 and sheath carriage screw 386.

Tube 380 includes an internal female thread including a linear female thread 383 along two portions of tube 380 and a partially helically-shaped female thread 382 along a portion of the tube disposed between the linear female thread portions 383. Both the rod carriage screw 378 and sheath carriage screw 386 include an internal male thread which engages the female threads of screw 374 and allows rotation of actuator 372 to translate to movement of the rod carriage screw 378 and sheath carriage screw 386. The sheath carriage screw 386 includes male nub(s) 385 which engage linear female thread 383 in the configuration shown in FIG. 17A. The sheath carriage screw 386 also has an outer male thread 387 (see FIG. 17D) which engages with an internal female thread in sheath carriage 384. FIG. 17A shows the delivery system in a configuration in which the implant is sheathed within the sheath and the posts are not locked to the buckles. Initial rotation of actuator 372 causes sheath carriage screw 386 to move linearly in the proximal direction. Because of the interaction between the male thread 387 and the female thread within sheath carriage 384, proximal movement of sheath carriage screw 386 causes proximal movement of the sheath carriage 384, as is shown in the transition from FIG. 17A to 17B. This movement causes proximal movement of sheath, such as is required to begin unsheathing the implant to allow it to self-expand.

This initial rotation of the actuator 372 does not, however, translate into proximal motion of rod carriage 376. This initial rotation of actuator 372 causes rod carriage screw 378 to move proximally, but because rod carriage screw 378 has a male nub (not shown) similar to the male nub 385 on the sheath carriage screw, the rod carriage screw rotates within outer tube 380. The rod carriage 376 has an internal female thread which mates with male thread 379 on the rod carriage screw 378. These threads allow the rod carriage screw 378 to rotate within rod carriage 376 without causing the rod carriage to move proximally. This initial rotation of actuator 372 thereby results in lost motion of the rod carriage 376, as is shown in the transition from FIG. 17A to 17B. As the sheath begins to be pulled back, the rods therefore do not pull on the posts.

In the configuration in FIG. 17B, both males nubs of the carriage screws are aligned with the respective linear female threads 383. Continued rotation of actuator 372 therefore results in proximal movement of both of the carriage screws 386 and 378. Because of the threaded interaction between the carriages and their respective screws, both carriages move in the proximal direction This is illustrated in the transition from FIG. 17B to 17C. During this portion of the procedure, both the sheath and the rods are being pulled in the proximal direction.

In the configuration in FIG. 17C, the bottom male nub 385 (not shown) engages helical thread 382. Continued rotation of actuator 372 therefore results in rotation of sheath carriage screw 386 relative to outer tube 380. This causes sheath carriage screw 386 to unscrew from sheath carriage 384, as is shown in the transition from FIG. 17C to FIG. 17D. This results in the sheath carriage not moving in the proximal direction (i.e., lost motion). The threaded interaction between rod carriage 376 and rod carriage screw 378, however, translates into proximal movement of the rod carriage 376, as is shown in the transition from FIG. 17C to 17D. During this portion of the procedure, the rods are being pulled proximally but the sheath is not being actuated.

The movements of the carriages can also be reversed by rotating the actuator in the opposite direction.

It should be noted that the female threads on lead screw 374 can have a different pitch along the length of the screw, as is shown in FIGS. 17A-17D (although the pitch of the thread on lead screw 374 may also be constant along the length of lead screw 374). As shown, the pitch is greater on the portion where the sheath carriage screw interacts with the lead screw 374 than the pitch where the rod carriage screw interacts with the lead screw 374. This results in the sheath carriage moving a greater distance that the rod carriage during the transition from FIG. 17B to 17C. Thus, FIGS. 17A-17D illustrate not only lost motion but a different rate of motion of two moving delivery system components based on actuation of a single actuator (e.g., the rotary actuator 202).

FIGS. 18A-18D illustrates a sequence of movements of male threaded element 412 over female threaded element 400 which has a varying pitch and a varying diameter. The lead screw 374 from FIGS. 17A-17D can have the varying pitch and diameter of female element 400, and the carriage screws in FIGS. 17A-17D can incorporate the features of male element 412. Section 402 has a smaller pitch than sections 404 and 406, while the diameter of section 406 is greater than the diameter in sections 402 and 404. The lead portion of male thread 410 has a greater height (see FIG. 18D), which allows it to engage female thread 406, 404, as well as 402. The male threads 408 have a smaller height than the lead portion. The male threads 408 are large enough to engage female threads 406, but not 404 or 402. This design allows for varying degrees of movement of male element 412 over the length of female threaded element 400. The male element 412 moves a greater distance when threaded in section 406 than in section 402, due to the difference in pitch. This can allow a delivery system component to move at first rate, followed by movement at a second rate (in this case, the second rate of movement is less than the first). This variable pitch design can be incorporated into any of the delivery systems described herein.

FIG. 19 illustrates a barrel cam design which functions with a variable pitch in a similar manner to the design shown in FIGS. 18A-18D. One difference between the two embodiments is that threads 433 and 435 in the embodiment in FIG. 19 are integrated into barrel housing 421 instead of a central lead screw. As shown in FIG. 19, sheathing carriage 425 rotates on first thread 433 and rod carriage 423 rotates on second thread 435 in barrel housing 421. Lost motion is accounted for by bringing the pitch angle to, or near to, 0 so the carriage rotates but does not translate (or translates a minimal amount) within barrel housing 421. Each of the carriages also includes nubs 429 for tracking in threads 433 and 435. The carriages also include holes 427 for guide tubes 431.

FIGS. 20A-20C illustrate an alternative design to account for lost motion including handle housing 452, a pair of gears 454, rotary actuator 456, rod lead screw 458, rod carriage 460, rod carriage spring 462, rod carriage screw 464, sheathing lead screw 466, sheath carriage 468, sheath carriage screw 470, sheath carriage spring 472. Rotary actuator 456 turns both gears 454, one geared to the rod lead screw 458 and one geared to the sheathing lead screw 466. Different pitches on each lead screw would allow for different linear motion rates for the rod screw 464 and sheathing screw 470. In an initial configuration shown in FIG. 20A, spring 462 is fully compressed and spring 472 is unloaded. Rotation of actuator 456 turns both lead screws 458 and 466, causing both the rod screw 464 and sheathing screw 470 to move proximally. The resistance to compression of spring 472 between the sheathing carriage 68 and sheathing lead screw 466 causes the sheathing carriage 468 to follow the proximal movement of sheathing screw 470, as is shown in the transition between FIGS. 20A and 20B. The force unloading of spring 462 causes the rod carriage 460 to remain stationary while rod screw 464 moves proximally, as is shown in the transition from FIG. 20A to FIG. 20B.

When the rod screw 464 reaches the proximal end of the rod carriage 460, continued rotation of actuator 456 causes both carriages to move, as is shown in FIG. 20B (both carriages in motion). Upon continued actuation of actuator 456, a stop (not shown in FIG. 20C) causes the sheathing carriage 468 to stop moving proximally. Continued rotation of the actuator 456 causes the continued movement of the sheath carriage screw 470 (but not sheath carriage 468) and the compression of spring 472. This allows for the locking of the anchor through proximal movement of the rod carriage 460 without motion of the sheath.

Actuating the actuator 456 in the reverse direction unlocks the anchor through distal motion of the rod carriage 460. Compression of spring 472 limits motion of the sheathing carriage 468 until the sheathing screw 470 is fully seated in the sheathing carriage 468. The two carriages then move together distally until the rod carriage 460 reaches a stop (not shown) causing the rod screw 464 to move distally while the rod carriage 460 does not move and spring 462 is compressed.

FIGS. 21-22 illustrate exemplary designs for decoupling the motion of the rods and outer sheath. In FIG. 21, a single actuator is geared to a gear with a cam on the proximal surface. The cam causes the engagement/disengagement of a clutch that is attached to a lead screw. When the clutch is engaged, the lead screw turns which causes a carriage (not shown) to move proximally or distally depending on the direction of movement of the actuator. When the clutch is not engaged, the lead screw does not turn and the carriage is stationary.

In FIG. 21 nut 502 (either for the rod or sheath) is connected to the carriage 504 (either for the rod or sheath) via a male tab 506 that engages with a female feature 508 in the carriage 504. The engagement between the nut 502 and the carriage 504 via the tab 506 causes the carriage 504 to move with the nut 502 as the lead screw 510 is turned (by an actuator not shown). The nut 502 has a nub 512 which travels along a path 514 in the housing. A jog 516 in the path 514 causes the nut 502 to rotate counterclockwise relative to the carriage 504. This motion causes the tab 506 to disengage from the female feature 508, releasing the nut 502 from the carriage 504. Since the nut 502 and carriage 504 are no longer joined, continued actuation (e.g., rotation) of the actuator moves only the nut 502. Rotating the actuator in the opposite direction causes the nut 502 to move back into contact with the carriage, reseating the nut tab 506 in the carriage and the carriage 504 then moves with the nut 502.

FIG. 22 shows a portion of delivery system 600 including lead screw 602 with region 606 with female thread and region 610 without threads. Sheath carriage 604 includes male threads 614 which engage with female threads 606 on lead screw 602. Sheath carriage 604 also includes lock element 608 which is adapted to engage with lock lip 612 on lead screw 602 to lock the carriage 604 onto lead screw and prevent the carriage 604 from moving in the distal direction D. Rotation of an actuator on the handle (not shown) causes lead screw 602 to rotate, which causes the carriage 604 to move proximally. This retracts the sheath in the proximal direction without moving the posts. Continued proximal movement causes lock element 608 to engage and lock with lock lip 612. Because the lead screw does not have any threads in region 610, continued rotation of lead screw 602 does not result in movement of the carriage 604.

FIGS. 23A and 23B illustrate a proximal portion of an exemplary handle which is used in the deployment of the heart valve shown in FIGS. 4 and 5A-5B. The handle includes housing 620, first actuator 624 in the form of a rotary actuator, slidable door 622, and second actuator 626 which can only be accessed when the door 622 has been slid forward from the first position in FIG. 25A to the second position in 25B. In this embodiment, rotary actuator 624 controls the movement of the sheath (such as is shown in FIGS. 3B-3F) and the movement of actuation elements 206B shown in FIGS. 4 and 5A-5B. In one embodiment, actuator 624 controls the movement of sheath and the actuation elements as shown in FIGS. 17A-17C, such that actuation of actuator 624 independently and dependently moves the sheath and actuation elements. Once the anchoring element is locked by the locking of posts to buckles, the physician slides door 622 to the position shown in FIG. 23B and actuates second actuator 626. Actuation of actuator 626 retracts pin assembly 236 in FIG. 4, which causes the three pins 234 to be removed from the bores through the posts and actuation elements, uncoupling the posts from the actuation elements 206B.

In one embodiment, continued actuation of actuator 626 also further retracts the actuation elements 206B from the position shown in FIG. 5B to the position shown in 5E. FIG. 23C illustrates an enlarged portion of handle 630 of an exemplary delivery system with a design which allows continued actuation of actuator 626 to further retract actuation elements 206B (second actuator 626 from FIGS. 23A and 23B not shown). The locking and sheathing drive ring actuates the locking and sheathing carriages via the lead screw similarly to the method described in reference to FIGS. 17A-17D. Handle 630 includes locking and sheathing drive ring 631, locking and sheathing lead screw 632, locking carriage 633, release pin carriage 635, lost motion barrel 629, release pin mandrels 636 (shown within hypotube), rod actuation mandrels 634 (shown within a hypotube), and force limiter 638. Force limiter 638 includes track 637 in which release pin carriage 635 moves when pulled proximally. The release collar actuates a separate smaller lead screw 639 (normally driven by locking carriage 633) which pulls proximally release pin carriage 635. When the physician is ready to remove the pins, the second actuator on the handle (not shown) is actuated, which engages the release lead screw 639, causing it to rotate. This pulls release collar 636 proximally in track 637, which causes release pin mandrels 636 to be pulled back proximally, releasing the pins from the posts and uncoupling the rods from the posts. Continued actuation of the second actuator continues to pull the release carriage until it reaches the proximal end of force limiter 638. When carriage 635 bottoms out on the proximal end of force limiter 638, it moves the portion of the force limiter in which it sits proximally relative to the other portion of the force limiter. This causes rod mandrels 634 to be pulled proximally, which pulls the rods in the proximal direction. Thus, the second actuator can be used to release the pins as well as continue to pull the rods back in the proximal direction.

Alternatively, the handle can be designed such that rotary actuator 624 can be further actuated to proximally retract actuation elements 206B after the pin has been removed. The delivery system can be then removed from the patient.

The medical implants described herein can be recollapsed and resheathed at least partially back inside the sheath after the entire implant has initially been deployed from the sheath. This is because at least a portion of the implant remains reversibly coupled to a portion of the delivery system after the implant is deployed from the sheath (e.g., see FIG. 3F). Even after the anchoring element is locked in the fully deployed configuration, the post can be unlocked from the buckle in some embodiments and thereafter the anchoring element can be resheathed into the sheath. Being able to resheath an implant after it has been deployed from a delivery sheath or catheter is advantageous because it allows for the implant to be removed from the patient or repositioned inside the patient if needed. For example, the functionality and/or positioning of a replacement heart valve can be assessed once the replacement heart valve is in the configuration shown in FIG. 3F (and continually assessed as the anchor begins to be locked in the expanded and locked configuration), and can then be resheathed and subsequently repositioned or removed from the patient if needed.

While the resheathing processes and delivery systems to perform the resheathing described herein make references to replacement heart valves, a wide variety of medical devices may benefit from the resheathing aids described herein. For example, an expandable stent which remains reversibly coupled to the delivery system after the stent has been deployed from a delivery catheter or sheath may benefit from having any of the resheathing aids described herein incorporated into the delivery systems thereof

To resheath the heart valve, the sheath is advanced distally relative to the catheter. Alternatively, the catheter can be withdrawn proximally relative to the sheath. Distal movement of the sheath relative to the catheter causes the fingers, which are coupled to the distal end of the catheter, to collapse radially inward. This causes the proximal end of the anchor to collapse. Continued distal movement of the sheath causes the rest of the heart valve to elongate and collapse, allowing the sheath to recapture the anchoring element.

In embodiments in which the anchoring element comprises a braided material, distal advancement of the sheath may result in portions of the proximal end of the anchor to get caught, or stuck, on the distal end of the sheath. This can prevent resheathing or it can reduce the resheathing efficiency.

FIG. 24 illustrates an alternative delivery system 640 including sheath 644, delivery catheter 646, and sheathing assist element 642. Sheathing assist element 642 is a braided structure, and can be similar to the braided anchoring elements described herein. The sheathing assist element 642 generally has a memory configuration in which the distal end of the sheathing assist element 642 has a diameter larger than the diameter of the proximal end of the anchoring element 649. The delivery system includes fingers 647 (only two can be seen) reversibly coupled to a proximal region of replacement heart valve 648 (replacement leaflets not shown for clarity). The proximal end of sheathing assist element 642 is coupled to the distal end of delivery catheter 646. Fingers 647 are also coupled to the distal end of catheter 646, and are generally “within” or radially inward relative to sheathing assist element 642. FIG. 24 shows a replacement heart valve after the sheath has been withdrawn, allowing the anchoring element to expand to a memory configuration, and has not yet been actively foreshortened.

To resheath the implant, the sheath is advanced distally relative to the catheter and implant. This can be done by actuating an actuator of a handle, as described above. Because the proximal end of the sheathing assist element is fixed to the distal end of the delivery catheter, the distal end of the sheath can easily pass over the proximal end of the sheathing assist element without getting caught. Continued distal movement of the sheath causes at least the distal portion of the sheathing assist element to elongate and partially collapse in diameter. As the sheathing assist element elongates, the distal end of the sheathing assist element moves distal relative to the proximal end of the anchor. Continued distal movement of the sheath continues to collapse the distal end of the sheathing assist element and at least a distal region of the sheathing assist element will engage at least the proximal end of the anchor. The sheathing assist element will therefore provide a surface over which the sheath can pass without the risk of getting caught on the proximal end of the anchor. The sheathing assist element may additionally apply a radially inward force to the proximal end of the anchor, assisting in the collapse of the proximal end of the anchor. As the sheath continues to be advanced distally, the anchor is collapsed and is resheathed back within the sheath. In some embodiments the sheathing assist element is a polymer mesh.

In some embodiments the sheathing assist element can also act as an embolic filter. Once unsheathed, the sheathing assist element can trap emboli traveling downstream to the target location, yet allowing blood to pass through the assist element. In such embodiments, the distal end of the sheathing assist element can be configured and arranged to have a memory diameter that is as close as possible to the diameter of the lumen in which it is to be disposed. Exemplary materials for embolic filters are known in the art.

FIGS. 25-28 illustrate alternative delivery systems with alternative sheathing assist element 660. Sheathing assist element 660 includes three (3) collapsible blades 662. The blades are fixed to one another at their proximal ends at hub 664 (see FIG. 28). Hub 664 is axially movable relative to fingers 666 and catheter 668, but the distal region of catheter 668 includes a hub stop 670 which is adapted to engage with the hub and prevent movement of the hub proximally relative to the hub stop. As sheath (not shown) is advanced distally over catheter 668, it begins to collapse fingers 666. As the fingers collapse radially inward, the hub can then move distally over the fingers. As the fingers collapse, the proximal end of the anchor begins to collapse and the hub continues to be advanced distally. Eventually the distal ends of blades 662 cover the proximal end of the anchor, and the sheath can then be advanced over the anchor without getting caught on the proximal end of the anchor. In some embodiments the blades are adapted to collapse inwards on themselves as the sheath applies a force to them.

In the embodiment shown in FIG. 26, sheathing assist element 660 includes optional finger openings 672 which are adapted to allow the fingers to be passed therethrough. Openings 672 can be designed to have any shape (e.g., rectangular, circular, etc) to allow the hub to be easily moved distally relative to the fingers. In the embodiment in FIG. 28, the blades have optional slits 674 to assist in their collapse.

FIG. 29 shows an embodiment of sheathing assist element 680 which include arms 682 and teeth 684 at their distal ends. The teeth are adapted to engage the crowns of the braid, which are formed where a brand strand turns at an end of the braid (or other proximal region of a non-braided anchor) and allow the sheath to be advanced distally over the anchor. Each arm 682 can have any number of teeth 684. The arms can be adapted to respond to an applied force from the sheath such that they change to a second configuration with a bend such that a distal portion of the arms are bent radially inward to engage the proximal end of the anchor.

FIG. 30 shows an alternative embodiment of a sheathing assist element 670 which is comprised of stent element 672. Sheathing assist element 670 functions similar to the embodiment shown in FIG. 26, but is not comprised of a braided material. The stent can be made from, for example, an alloy or any other suitable material as is known in the art of stents.

FIG. 31 shows an alternative embodiment of sheathing assist element 680 which includes curled elements 682 (anchor not shown). The proximal end of the curled elements 682 can be coupled to a hub as described above in other embodiments, or each of the curled elements can be individually affixed to the catheter. As the sheath is advanced distally, the force of the sheath causes the distal ends of the curled elements to uncurl and straighten. The distal ends of the straightened element extend over and distal to the proximal end of the anchor, and allow the sheath to be advanced over the proximal end of the anchor without getting caught on the crowns of the anchor. The curled elements can be made of, for example, stainless steel or any other suitable material.

In an alternative embodiment shown in FIGS. 32 and 33, sheathing assist element 684 comprises a plurality of arms 686 (twelve arms are shown in FIGS. 32 and 33), each which have a distal end with male locking element 688. Each arm 686 includes female locking element 690 disposed closer to hub 692 than the male locking element 688. In FIGS. 32 and 33, the male locking elements have an arrowhead shape and the female lock elements are slot-shaped. Hub 692 includes an opening 694 therein to allow control wire 696 to pass therethrough. Control wire 696 has an enlarged element at its distal end (not shown) which prevents the enlarged element from being pulled proximally through opening 694. In the delivery configuration, each arm 686 extends distally from hub 692 and the distal region of each arm distal to the slot is wrapped around a crown of the anchor (see FIG. 33). The male lock elements 688 are engaged with female lock elements 690. When the replacement heart valve is to be resheathed, a proximally directed force is applied to the control wire 696, which prevents the crowns from extending radially outward, thus allowing the sheath to be advanced distally over the crowns of the proximal end without getting stuck. Alternatively, a proximal force is not required, and the engagement of arms 686 and the crowns of the anchor prevent the crowns from getting stuck on the sheath. A proximally directed force on the hub will release the arrowheads from the slots, releasing the arms from the anchors. This releases the implant from the arms.

In alternative embodiments shown in FIGS. 34-37, the delivery systems include wires or sutures 700 which are coupled at their proximal ends to a delivery system component (e.g., the distal end of catheter 702, an actuator in a handle, etc.), and are each wrapped around a crown of the anchor. The distal ends of wires or sutures 700 have an enlarged element 704 such as a spherical element which is adapted to engage with annular detent 706 in the outer surface of catheter 702. Sheath 708 maintains the engagement of the enlarged element 704 and detent 706. The distal end of the wire or suture 700 can simply comprise one locking element while the catheter outer surface can include a second locking element. The sutures 700 provide a radially inward force to the crowns, helping the sheath extend over them during resheathing. Once the outer sheath is pulled proximally relative to the catheter, the enlarged element is released from the indent, and the wire/suture 700 can be released from the crowns of the anchor. In the alternative exemplary embodiment shown in FIG. 35 the catheter includes multiple detents 706.

FIGS. 38-41 illustrate an alternative embodiment of sheathing assist 710, which includes a plurality of arms attached to the distal end of catheter 714. The arms include two types of arms 718 and 720, wherein arms 718 are slightly longer than arms 720. The arms are formed from a wire segment with a bend at their distal ends, wherein the two ends of the arms are coupled together at the proximal end 726 of the sheathing assist 710. Arms 718 extend from the catheter to the anchor and the distal ends are weaved into the braid of the anchor. That is, the distal ends of arms 718 are disposed radially within the braided anchor, as can be seen in FIGS. 39-41. Arms 718 are attached to stiffening elements 722, which are shorter than both arms 718 and arms 720. Stiffening element 722 is attached to arm 718 at attachment point 724, which can be, for example, a weld. As can be seen, stiffening elements 722 are disposed within the wire segments of arms 718, which increases the strength of arms 718. Sheathing assist also includes arms 720 which are shown shorter than arms 718, although they could both be substantially the same length. As can be seen in FIG. 38, two arms 720 are attached together at attachment points 724. Arms 720 are positioned radially outwards of braid, unlike arms 720 which are weaved into the braid and disposed radially inside the braid. Arms 720 help apply a radially inward force on the braid as the sheath is advanced distally. Arms 718 also help apply a radially inward force on the braid as well, and the two sets of arms ensure that the distal end of the sheath doesn't get caught on the anchor.

In an alternative embodiment, the proximal crowns of the braided anchor are heat-set in a configuration in which the crowns are bent radially inward (relative to longitudinal axis of the braid and relative to the rest of the anchor), to assist the sheath in the resheathing process. The crowns are bent inward to prevent the sheath from getting caught on the crowns.

Although the present disclosure has been described in connection with the exemplary embodiments described above, those of ordinary skill in the art will understand that many modifications can be made thereto. Accordingly, it is not intended that the scope of the present disclosure in any way be limited by the above exemplary embodiments. 

1. A medical device system, including: a delivery system comprising a housing disposed external to a subject, wherein the housing comprises an actuator, wherein the delivery system is configured and arranged such that the actuator is adapted to move a first delivery system component independently of a second delivery system component, and wherein the delivery system is further configured and arranged such that actuator is also adapted to move the second delivery system component independently of the first delivery system component. 